EP0139548B1 - Einrichtung zur Regulierung einer Pumpe - Google Patents

Einrichtung zur Regulierung einer Pumpe Download PDF

Info

Publication number
EP0139548B1
EP0139548B1 EP84401634A EP84401634A EP0139548B1 EP 0139548 B1 EP0139548 B1 EP 0139548B1 EP 84401634 A EP84401634 A EP 84401634A EP 84401634 A EP84401634 A EP 84401634A EP 0139548 B1 EP0139548 B1 EP 0139548B1
Authority
EP
European Patent Office
Prior art keywords
circuit
pump
pressure
signal
organ
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Expired
Application number
EP84401634A
Other languages
English (en)
French (fr)
Other versions
EP0139548A1 (de
Inventor
Alain Pieronne
Régis Logier
Michel Delecroix
Georges Soots
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Universite Lille 2 Droit et Sante
Original Assignee
Universite Lille 2 Droit et Sante
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Universite Lille 2 Droit et Sante filed Critical Universite Lille 2 Droit et Sante
Priority to AT84401634T priority Critical patent/ATE37790T1/de
Publication of EP0139548A1 publication Critical patent/EP0139548A1/de
Application granted granted Critical
Publication of EP0139548B1 publication Critical patent/EP0139548B1/de
Expired legal-status Critical Current

Links

Images

Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
    • A61M1/36—Other treatment of blood in a by-pass of the natural circulatory system, e.g. temperature adaptation, irradiation ; Extra-corporeal blood circuits
    • A61M1/3621—Extra-corporeal blood circuits
    • A61M1/3639—Blood pressure control, pressure transducers specially adapted therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3344—Measuring or controlling pressure at the body treatment site
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/33—Controlling, regulating or measuring
    • A61M2205/3331—Pressure; Flow
    • A61M2205/3351—Controlling upstream pump pressure

Definitions

  • the invention relates to a device for regulating the speed of a pump of an assistance system for a living organ and to the assistance system for a living organ provided with this device.
  • this extracorportal circulation (C.E.C) has the role of ensuring the function of the heart and the lung during their exclusion during intra-cardiac surgical operations.
  • the left assistance is therefore intended for patients who have a myocardial condition and do not allow weaning from the "C.E.C” despite the use of catecholamines and intra-aortic counterpulsation.
  • the left assistance circuit which is the subject of the invention does not use the same parameters and, therefore, its regulation as a function of the quantity of blood cannot be suitable.
  • P.O.G left atrial pressure di-after called "P.O.G” because the variations in particular abrupt of flow, pressure and volemia, would be badly supported by the patients in cardiogenic shock.
  • a result which the invention aims to obtain is a device which regulates the flow in the organism and therefore which, in the example chosen regulates the left ventricular leads and which, if necessary, can also control a simultaneous right ventricular lead circuit.
  • the invention is particularly characterized in that at least one of the means for measuring the real operating conditions consists of a pressure measurement means.
  • the invention also relates to the assistance system provided with this device.
  • the left assistance circuit in a manner comparable to that of a CEC, comprises a cannula 1 sutured at the outlet of the organ such as the level of the tip of the left ventricle 2 or the level of the left atrium and which ensures a discharge of this organ.
  • non-metallic connection By a non-metallic connection (not shown) it is connected to the input of a circuit 3, for example made of polyvynil chloride.
  • This circuit first passes through an air purge 4 then through a possible inlet 5 of a product, such as heparin, and a bubble detector 6 before arriving in a pump 7 with rotary rollers 8 whose speed is adjustable according to the potential difference applied to its terminals.
  • the arterial line passes through a filter 9 upstream and downstream of which two outlets 10, 11 are provided which allow pressure taps on either side of the filter 9 which itself is interchangeable.
  • the circuit 3 Before arriving at a second cannula 14 intended for reinjection into the inlet of the organ, for example at the level of the aorta 15, the circuit 3 continues possibly passing through a system without heparin or through an inlet 12 of product, like protamine, then by a new air purge 13.
  • the possible straight assistance circuit it is similar to the previous one since it comprises for example, firstly a cannula 16 sutured at the outlet of the organ, such as the cava veins, and which, by a non-metallic connection is connected to a circuit 17 first passing through an air purge 4a and a possible inlet 5a of product such as heparin before reaching a pump 6a then a filter 9a upstream and downstream of which entries 10a. 11g allow pressure taps.
  • the circuit is connected to a pulmonary cannula 18.
  • the pump 7, 7a is of a type whose flow rate is linked to the potential difference applied to its terminals.
  • the circuit includes a regulating device 21.
  • This device operates in particular by reference to the real pressure in the organ, pressure hereinafter called "P.O.G", and to a desired pressure called set pressure or preprogrammed.
  • both the flow 22 in the left circuit 3 and that 23 in the possible right circuit 17 increase according to a predetermined slope to arrive at optimum flow.
  • the alarm ports are such that if the P.O.G. real fall of a value lower than a given value (for example five millimeters of mercury), they cause an audible alarm and a pump stop.
  • a given value for example five millimeters of mercury
  • the regulating device 21 further comprises means for comparing the pressure measured in the outlet 11 downstream of the filter 9 with respect to a preprogrammed given pressure value, different from the set pressure, as well as means for comparing the pressures in the outputs 10, 11 upstream and downstream of said filter, the difference in these pressures causes the filter clogging alarm.
  • the first means In combination with a bend 25 in the part of the circuit located downstream of the pump 7, the first means detect any overpressure.
  • the said means When this difference reaches a preprogrammed given value, the said means then activate the audible and visual alarms indicating this type of problem.
  • the said device also comprises a means of semi-quantitative evaluation of bubbles with auditory control.
  • the device also includes a weaning system by decrementing the assistance flow rate, for example of about one hundred milliliters every hour.
  • the device may also include a "reset” button to stop the audible alarm, the visual alarm remaining on as long as the fault persists.
  • the flow rate of the corresponding pump 7a will be regulated by the same device 21 as that of the pump 7 of the left assistance.
  • the device will simply include a means, such as a potentiometer, making it possible to vary, in sufficient proportions, the straight flow rate with respect to the left flow rate, by adjusting the potential difference applied to the terminals of the right pump 7a with respect to that of the left pump 7, and this, for example from more said percent to minus fifteen percent.
  • a means such as a potentiometer
  • the means varying this potential difference and therefore of flow rate are controlled by the P.O.G.
  • the regulation of the pump flow is done using a DC voltage which is varied, for example, from zero to fifteen volts.
  • the device is provided with means for over-modulation of this voltage.
  • the device can comprise means such that the electrocardiogram obtained can advantageously be returned to the regulator which then comprises on the one hand means for setting in the form of the electrical inter-systolic space, called "RR space” and on the other hand two potentiometers 26, 27 making it possible to determine, with respect to the preceding RR space, the duration, the moment and the intensity of l pump acceleration regardless of any other factor.
  • RR space means for setting in the form of the electrical inter-systolic space
  • two potentiometers 26, 27 making it possible to determine, with respect to the preceding RR space, the duration, the moment and the intensity of l pump acceleration regardless of any other factor.
  • the start of the pulse will be between zero and - sixty percent of the R.R. time, the end of the pulse between forty and one hundred percent of the R.R. time.
  • the amplitude is adjusted to allow a diastolic ejection of twenty to forty milliliters.
  • the regulating device 21 has been built around a microprocessor of the so-called "Z80" type.
  • the input members 31 (FIGS. 4 and 5) of the block 28 for shaping the input signals mainly comprise a means 32 for inputting the POG taken by the means 24, coding wheels 33 and inputs 34 in from security organs.
  • block 28 To use POG, it is necessary for block 28 to include means 32 for transforming POG into electrical voltage and for this means 32 to be such that it gives not only the voltage representing the instantaneous pressure but also the voltages corresponding to the alarms. high and low POG
  • the encoder wheels 33 will give the computer 29 the value of P.O.G to be reached (set pressure) to allow it to adapt the flow rate accordingly.
  • the inputs 34 from security organs will be of two main types including, one, those controlling the stopping of the pump, the other, those controlling so-called "normal” alarms.
  • the inputs controlling normal alarms include the input 38 of the signal from the pressure module and indicating a POG greater than a fixed limit and the input of the signal 39 of the pressure difference calculated from the pressures 40 and 41 coming from the inputs 10, 11 pre and post-filter of the circuit and signal if filter 9 is clogged.
  • the device will include the corresponding inputs which will preferably be distributed over different ports, namely on a port 55 for the inputs controlling the alarms. "nor males "and on a port 56 for the inputs controlling the stopping of the pump 7, 7a,
  • the computer 29 After processing the input information, the computer 29 delivers, among other signals, a command which is intended for the pump but which is of digital type and which must first be transformed into electrical voltage.
  • the pump 7, 7a uses, to be regulated, a direct or modulated voltage between zero and fifteen volts.
  • circuit 30 for shaping the output signals (FIGS. 4 and 6) which therefore includes digital-analog conversion means 62 and leveling means 63.
  • the output circuit 30 also comprises means 64 to 70 for displaying the alarms such as light-emitting diodes and an audible alarm 71 such as a loudspeaker 72 excited by a low frequency oscillator 73.
  • the device comprises an operational amplifier with variable gain controlling on the basis of the signal from the left pump 7, the pump 7a of the right circuit.
  • the speed of the right pump relative to the left pump will be manually adjustable by adjusting this gain.
  • port 74 possibly controls the stopping of the two pumps while the alarms of the left and / or right circuit (not shown) are controlled through ports 75, 76 and the computer 29.
  • the signals then pass through a shaping means 85 then through a potentiometer 86 for leveling the pulsed volume before arriving at their mixer 87 with the signal coming from the microprocessor and called pump voltage.
  • the flow is pulsed by acceleration of the pump, via, if the heart is in ventricular fibrillation, an internal trigger with fixed frequency possibly adjusting the rising and falling edges relative to the EKG as well as the amplitude of the pulse and the duration.

Landscapes

  • Health & Medical Sciences (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Hematology (AREA)
  • Cardiology (AREA)
  • Animal Behavior & Ethology (AREA)
  • Engineering & Computer Science (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • External Artificial Organs (AREA)
  • Lubrication Of Internal Combustion Engines (AREA)
  • Control Of Positive-Displacement Pumps (AREA)
  • Control Of Fluid Pressure (AREA)
  • Infusion, Injection, And Reservoir Apparatuses (AREA)

Claims (10)

1. Vorrichtung (21) zur Steuerung der Geschwindigkeit und also insbesondere des Durchsatzes zumindest einer Pumpe (7, 7a) eines Assistenz-Systems eines lebenden Organs wie der Herzmuskel, wobei das System hauptsächlich einen Kreislauf (3, 17) aufweist, der mit seinen Enden (1 und 14 oder 16 und 18) mit dem Ausgang (2) und dem Eingang (15) besagten Organes verbunden ist, und in diesen Kreislauf (3, 17) besagte Pumpe (7,7a) eingeschaltet ist, beispielsweise mit Reibrollen (8, 8a), die durch einen Motor mit variabler Geschwindigkeit gesteuert ist, wobei die Vorrichtung aufweist:
- Meßmittel (10, 11, 24) und zum Speichern der tatsächlichen Funktionsbedingungen,
- Mittel zum Verarbeiten und zum Speichern der entsprechenden Funktions-Einstellwerten,
- Mittel (29) zum Vergleich jedes reellen Werts mit einem entsprechenden Einstellwert und zur Verarbeitung eines zu dem Unterschied zwischen den beiden Werten proportionalen Signals,
- Verarbeitungsmittel als Funktion dieses proportionalen Signals eines weiteren Signals, das die Geschwindigkeit der Pumpe bestimmt,
- Steuertore für den Schwellwert eines jeden der proportionalen Signale und
- Warnrufe, von denen jeder durch einer der proportionalen Signale gesteuert wird beim Übersteigen der festgelegten Schwelle, dadurch gekennzeichnet, daß zumindest eines der Meßmittel für die reellen Funktionsbedingungen aus einem Druckmeßmittel besteht.
2. Vorrichtung nach Anspruch 1, dadurch gekennzeichnet, daß zumindest eines (24) der Druckmeßmittel (10, 11, 24) aus einem Abgriffelement für Informationen besteht, das in das Innere des lebenden zu unterstützenden Organs eindringt.
3. Vorrichtung nach Anspruch 2, dadurch gekennzeichnet, daß außerdem die Mittel zumindest als Funktion des Drucks in dem Organ das proportionale Signal verarbeiten, welches die Geschwindigkeit der Pumpe des ersten Kreises bestimmt, wobei die Vorrichtung einen Verstärker mit durch ein Potentiometer einstellbarer Verstärkung aufweist und der, ausgehend von diesem Signal ein zweites, mit dem ersten Signal in regelbaren Bereichen vergleichbares Signal verarbeitet und die Pumpe (7a) eines zweiten Unterstützungskreises (17) für ein Organ steuern kann, in welchem der Durchsatz physiologisch nahe wenn nicht identisch zu dem ersteren ist.
4. Vorrichtung nach einem der Ansprüche 1 bis 3, dadurch gekennzeichnet, daß die Vorrichtung eine Vorrichtung zur Auf-/Übermodulation des die Geschwindigkeit der Pumpe bestimmendes Signal aufweist.
5. Vorrichtung nach einem der Ansprüche 1 bis 4, dadurch gekennzeichnet, daß der Schaltkreis ein Mittel (6) zum Nachweis von Blasen aufweist.
6. Vorrichtung nach einem der Ansprüche 1 bis 5, dadurch gekennzeichnet, daß sie Mittel, die automatisch und zunehmend das Signal modifizieren, welches die Geschwindigkeit der Pumpe bestimmt, und zwar im Sinne einer Abnahme dieser Geschwindigkeit und infolgedessen des Durchsatzes und Mittel aufweist, die im Fall des Drucks in dem Organ den Mißerfolg des Abtrennens interpretieren, sofort die Verkleinerung anhalten und ein Signal wiederherstellen, welches die Zurückkehr zu der vorhergehenden Geschwindigkeit bestimmt.
7. Unterstützungssystem für ein lebendes Organ wie der Herzmuskel, mit hauptsächlich einem Kreis (3, 17), der mit seinen Enden (1 und 14 oder 16 und 18) mit dem Ausgang (2) und dem Eingang (15) des besagten Organes verbunden ist, und in diesem Kreis (3, 17) besagte Pumpe (7, 7a), beispielsweise mit Reibrollen (8, 8a) eingeschaltet ist, die durch einen Motor mit variabler Geschwindigkeit gesteuert ist, wobei das System dadurch gekennzeichnet ist, daß es eine Vorrichtung zum Steuern gemäß einem der Ansprüche 1 bis 6 aufweist.
8. System nach Anspruch 7, dadurch gekennzeichnet, daß in den Kreis ein Filter eingeschaltet ist und daß die Mittel (10, 11) der Vorrichtung, die die Information über den Druck in dem Kreis abnehmen, mit dem Kreis stromaufwärtig und stromabwärtig von diesem Filter verbunden sind.
9. System nach Anspruch 7 oder 8, dadurch gekennzeichnet, daß in den Kreis eine Nachweisvorrichtung für Blasen eingeschaltet ist und daß die Vorrichtung Mittel aufweist, die die Pumpe des Kreises bei Nachweis der besagten Blasen anhält.
10. System nach Anspruch 8 oder 9, dadurch gekennzeichnet, daß mit Hinblick auf die Erleichterung des Nachweises eines Überdrucks durch die Mittel zum Messen des Drucks, die stromaufwärts des Filters angeordnet sind, der Schaltkreis stromabwärtig von der Pumpe eine Kröpfung (25) aufweist.
EP84401634A 1983-08-08 1984-08-06 Einrichtung zur Regulierung einer Pumpe Expired EP0139548B1 (de)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AT84401634T ATE37790T1 (de) 1983-08-08 1984-08-06 Einrichtung zur regulierung einer pumpe.

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
FR8313236A FR2550583B1 (fr) 1983-08-08 1983-08-08 Dispositif de regulation d'une pompe
FR8313236 1983-08-08

Publications (2)

Publication Number Publication Date
EP0139548A1 EP0139548A1 (de) 1985-05-02
EP0139548B1 true EP0139548B1 (de) 1988-10-12

Family

ID=9291583

Family Applications (1)

Application Number Title Priority Date Filing Date
EP84401634A Expired EP0139548B1 (de) 1983-08-08 1984-08-06 Einrichtung zur Regulierung einer Pumpe

Country Status (8)

Country Link
US (1) US4662355A (de)
EP (1) EP0139548B1 (de)
JP (1) JPS60501941A (de)
AT (1) ATE37790T1 (de)
DE (1) DE3474512D1 (de)
DK (1) DK137685A (de)
FR (1) FR2550583B1 (de)
WO (1) WO1985000754A1 (de)

Families Citing this family (53)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPS61232859A (ja) * 1985-04-05 1986-10-17 呉羽化学工業株式会社 医用ポンプ装置
GB2196854B (en) * 1985-11-12 1990-02-14 Electro Catheter Corp External pulsatile cardiac assist device
SE452405B (sv) * 1985-12-19 1987-11-30 Gambro Cardio Ab Hjert-lungsystem avsett for syresettning av en patients blod
US4782817A (en) * 1987-05-29 1988-11-08 Abiomed Cardiovascular, Inc. Ventricular support system
IL85249A0 (en) * 1988-01-29 1988-07-31 Galram Technology Ind Ltd Heart assist device
JPH0321257A (ja) * 1989-01-31 1991-01-30 Aisin Seiki Co Ltd 血液ポンプの駆動装置
US5458571A (en) * 1989-03-17 1995-10-17 Merit Medical Systems, Inc. System and method for monitoring, displaying and recording balloon catheter condition interval data
US5453091A (en) * 1989-03-17 1995-09-26 Merit Medical Systems, Inc. RF transmission module for wirelessly transmitting balloon catheter data in a syringe inflation system
US5449345A (en) * 1989-03-17 1995-09-12 Merit Medical Systems, Inc. Detachable and reusable digital control unit for monitoring balloon catheter data in a syringe inflation system
US5431629A (en) * 1989-03-17 1995-07-11 Merit Medical Systems, Inc. System and method for monitoring, displaying and recording balloon catheter condition interval data
US5425713A (en) * 1989-03-17 1995-06-20 Merit Medical Systems, Inc. System and method for monitoring, displaying and recording balloon catheter condition interval and inflation location data
US4995857A (en) * 1989-04-07 1991-02-26 Arnold John R Left ventricular assist device and method for temporary and permanent procedures
US4955856A (en) * 1989-06-30 1990-09-11 Phillips Steven J Method and apparatus for installing a ventricular assist device cannulae
US5062775A (en) * 1989-09-29 1991-11-05 Rocky Mountain Research, Inc. Roller pump in an extra corporeal support system
US5376114A (en) * 1992-10-30 1994-12-27 Jarvik; Robert Cannula pumps for temporary cardiac support and methods of their application and use
US5645531A (en) * 1993-05-26 1997-07-08 Quest Medical, Inc. Constant pressure blood mixture delivery system and method
US5759148A (en) * 1995-10-18 1998-06-02 Sipin; Anatole J. Controlled pneumatic driving system
JP3366808B2 (ja) * 1996-07-18 2003-01-14 株式会社日立製作所 電子財布
US5965089A (en) * 1996-10-04 1999-10-12 United States Surgical Corporation Circulatory support system
US5957879A (en) * 1997-01-24 1999-09-28 Heartport, Inc. Methods and devices for maintaining cardiopulmonary bypass and arresting a patient's heart
US5964694A (en) * 1997-04-02 1999-10-12 Guidant Corporation Method and apparatus for cardiac blood flow assistance
US7083588B1 (en) * 1998-05-26 2006-08-01 Medtronic Vascular, Inc. Apparatus for providing coronary retroperfusion and methods of use
US20010027287A1 (en) * 1998-05-26 2001-10-04 Trans Vascular, Inc. Apparatus for providing coronary retroperfusion and/or left ventricular assist and methods of use
US8091556B2 (en) 2001-04-20 2012-01-10 V-Wave Ltd. Methods and apparatus for reducing localized circulatory system pressure
WO2005074367A2 (en) * 2004-02-03 2005-08-18 Atria Medical Inc. Device and method for controlling in-vivo pressure
NZ523300A (en) * 2002-12-20 2005-12-23 Impian Technologies Ltd Peristaltic pump head and tube holder
MXPA04000801A (es) * 2003-01-29 2005-06-17 Innovamedica S A De C V Anastomosis auricular-arterial de bajo flujo para revascularizacion del miocardio auxiliada por bomba sin derivacion cardiopulmonar.
JP4094600B2 (ja) * 2004-10-06 2008-06-04 日機装株式会社 血液浄化装置
US9681948B2 (en) 2006-01-23 2017-06-20 V-Wave Ltd. Heart anchor device
US8092416B2 (en) 2008-03-28 2012-01-10 Vitalmex Internacional S.A. De C.V. Device and method for connecting a blood pump without trapping air bubbles
US8329450B2 (en) * 2008-08-01 2012-12-11 Biomedinnovations, Llc Methods and apparatus for organ support
US20210161637A1 (en) 2009-05-04 2021-06-03 V-Wave Ltd. Shunt for redistributing atrial blood volume
US9034034B2 (en) 2010-12-22 2015-05-19 V-Wave Ltd. Devices for reducing left atrial pressure, and methods of making and using same
WO2010128501A1 (en) 2009-05-04 2010-11-11 V-Wave Ltd. Device and method for regulating pressure in a heart chamber
US10076403B1 (en) 2009-05-04 2018-09-18 V-Wave Ltd. Shunt for redistributing atrial blood volume
US11135054B2 (en) 2011-07-28 2021-10-05 V-Wave Ltd. Interatrial shunts having biodegradable material, and methods of making and using same
US9629715B2 (en) 2011-07-28 2017-04-25 V-Wave Ltd. Devices for reducing left atrial pressure having biodegradable constriction, and methods of making and using same
US9713696B2 (en) 2013-05-21 2017-07-25 V-Wave Ltd. Apparatus and methods for delivering devices for reducing left atrial pressure
EP3291773A4 (de) 2015-05-07 2019-05-01 The Medical Research, Infrastructure, And Health Services Fund Of The Tel Aviv Medical Center Temporäre interatriale shunts
US10835394B2 (en) 2016-05-31 2020-11-17 V-Wave, Ltd. Systems and methods for making encapsulated hourglass shaped stents
US20170340460A1 (en) 2016-05-31 2017-11-30 V-Wave Ltd. Systems and methods for making encapsulated hourglass shaped stents
US11291807B2 (en) 2017-03-03 2022-04-05 V-Wave Ltd. Asymmetric shunt for redistributing atrial blood volume
JP7033145B2 (ja) 2017-03-03 2022-03-09 ブイ－ウェーブ リミテッド 心房血液体積を再分配するためのシャント
US10898698B1 (en) 2020-05-04 2021-01-26 V-Wave Ltd. Devices with dimensions that can be reduced and increased in vivo, and methods of making and using the same
WO2019142152A1 (en) 2018-01-20 2019-07-25 V-Wave Ltd. Devices and methods for providing passage between heart chambers
US11458287B2 (en) 2018-01-20 2022-10-04 V-Wave Ltd. Devices with dimensions that can be reduced and increased in vivo, and methods of making and using the same
US11176849B2 (en) * 2018-10-29 2021-11-16 The Aga Khan University Pumping heart simulator
US11612385B2 (en) 2019-04-03 2023-03-28 V-Wave Ltd. Systems and methods for delivering implantable devices across an atrial septum
CN114096205B (zh) 2019-05-20 2024-05-24 V-波有限责任公司 用于产生房间分流管的系统和方法
US11801369B2 (en) 2020-08-25 2023-10-31 Shifamed Holdings, Llc Adjustable interatrial shunts and associated systems and methods
WO2022103973A1 (en) 2020-11-12 2022-05-19 Shifamed Holdings, Llc Adjustable implantable devices and associated methods
US11234702B1 (en) 2020-11-13 2022-02-01 V-Wave Ltd. Interatrial shunt having physiologic sensor
WO2023199267A1 (en) 2022-04-14 2023-10-19 V-Wave Ltd. Interatrial shunt with expanded neck region

Family Cites Families (15)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3457909A (en) * 1966-07-20 1969-07-29 Avco Corp Heart augmentation system provided with means for measuring intra-arterial pressure
US3771174A (en) * 1972-04-28 1973-11-13 D Wortman Artificial heart utilizing blood pulsing fluid oscillators
US3882861A (en) * 1973-09-24 1975-05-13 Vital Assists Auxiliary control for a blood pump
DE2455229A1 (de) * 1974-11-21 1976-05-26 Stoeckert Instr Apparatebau Gm Herzlungenmaschine und insbesondere partielle bypass-maschine
US4080958A (en) * 1976-02-27 1978-03-28 Datascope Corporation Apparatus for aiding and improving the blood flow in patients
FR2366023A1 (fr) * 1976-07-30 1978-04-28 Inst Nat Sante Rech Med Procede et appareil de reglage des conditions d'hemodialyse
CA1119971A (en) * 1976-09-07 1982-03-16 James T. Hutchisson Hemodialysis system with modular dialysate manifold assembly
US4116589A (en) * 1977-04-15 1978-09-26 Avco Corporation Extracorporeal pulsatile blood pump comprised of side by side bladders
DE2823802C2 (de) * 1978-05-31 1982-05-27 Speidel + Keller Gmbh + Co Kg, 7455 Jungingen Antriebsanordnung einer oszillierenden Verdrängerpumpe
US4223672A (en) * 1979-02-08 1980-09-23 Baxter Travenol Laboratories, Inc. Variable volume plasma treatment chamber for an apparatus for the extracorporeal treatment of disease
FR2471193A1 (fr) * 1979-12-12 1981-06-19 Inst Nat Sante Rech Med Dispositif et moyens pour la regulation du debit de sang delivre par un systeme de circulation extracorporelle
FR2502499B1 (fr) * 1981-03-27 1987-01-23 Farcot Jean Christian Appareil pour la retroperfusion sanguine, destine notamment au traitement d'infarctus par injection de sang arteriel dans le sinus coronaire
US4493693A (en) * 1982-07-30 1985-01-15 Baxter Travenol Laboratories, Inc. Trans-membrane pressure monitoring system
US4486189A (en) * 1982-09-24 1984-12-04 Extracorporeal Medical Specialties, Inc. Dual mode hemodialysis system
US4540399A (en) * 1983-02-01 1985-09-10 Ken Litzie Emergency bypass system

Also Published As

Publication number Publication date
DK137685D0 (da) 1985-03-27
JPS60501941A (ja) 1985-11-14
FR2550583A1 (fr) 1985-02-15
US4662355A (en) 1987-05-05
EP0139548A1 (de) 1985-05-02
DE3474512D1 (en) 1988-11-17
DK137685A (da) 1985-03-27
FR2550583B1 (fr) 1986-03-28
ATE37790T1 (de) 1988-10-15
WO1985000754A1 (fr) 1985-02-28

Similar Documents

Publication Publication Date Title
EP0139548B1 (de) Einrichtung zur Regulierung einer Pumpe
US9259521B2 (en) Method and apparatus for monitoring and optimizing blood circulation generated by a pump
EP0886529B1 (de) VORRICHTUNG ZUR BESTIMMUNG DER BLUTREZIRKULATION IN EINEm VASKULäREN ZUGANG
JP3812978B2 (ja) 体外血液療法中に血流力学的パラメーターを決定するための装置
CN101945677B (zh) 血量监测器与血液治疗设备
WO2010040927A1 (fr) Appareil de traitement extracorporel de sang et procede de gestion d'un tel appareil
SE449303B (sv) Kardioplegisk styr- och reglerapparat
JP2009268922A (ja) アクセス流を測定するための方法及び装置
EP0778783A1 (de) Verfahren und gerät für die automatische hämodialyse
US11793994B2 (en) Use of cardiac assist device to improve kidney function
US20210052219A1 (en) Pump homeostasis indicator (phi)
US20220387778A1 (en) Intravascular blood pump and hemodynamic support system with blood flow pulsatility validity monitoring and invalidity detection with alarm
EP0029793B1 (de) Apparatur zur Überwachung von Hemodialyse-Behandlungen
EP0551043B1 (de) Verfahren und Vorrichtung zur Überwachung eines Hämodialysevorganges
Shoukas Carotid sinus baroreceptor reflex control and epinephrine. Influence on capacitive and resistive properties of the total pulmonary vascular bed of the dog.
EP1136089A2 (de) Verfahren zur Analyse von Druckänderungen in einem Infusionsvorrichtung mit mehrerer Infusionsmodule
Teman et al. A novel rotary pulsatile flow pump for cardiopulmonary bypass
FR2872707A1 (fr) Dispositif d'assistance circulatoire pour le coeur
WO2024017840A1 (fr) Dispositif d'assistance ou de suppléance du cœur
WO2023126192A1 (fr) Dispositif d'assistance ou de suppléance du coeur
FR3131542A1 (fr) Dispositif d’assistance ou de suppléance du cœur.
FR3131540A1 (fr) Dispositif d’assistance ou de suppléance du cœur.
FR3131539A1 (fr) Canule d’admission d’un dispositif d’assistance ou de suppléance du cœur.
EP0030760A1 (de) Durchflussregelvorrichtung für Blut, welches durch ein Extrakorporalumlaufsystem abgegeben wird, Messfühler für eine Flüssigkeitsmenge und Induktionsgeber für diese Vorrichtung
WO2024056358A1 (fr) Dispositif d'assistance ou de suppléance du cœur

Legal Events

Date Code Title Description
PUAI Public reference made under article 153(3) epc to a published international application that has entered the european phase

Free format text: ORIGINAL CODE: 0009012

17P Request for examination filed

Effective date: 19841220

AK Designated contracting states

Designated state(s): AT BE CH DE FR GB IT LI NL SE

17Q First examination report despatched

Effective date: 19870610

RAP1 Party data changed (applicant data changed or rights of an application transferred)

Owner name: UNIVERSITE DU DROIT ET DE LA SANTE LILLE II

RIN1 Information on inventor provided before grant (corrected)

Inventor name: SOOTS, GEORGES

Inventor name: DELECROIX, MICHEL

Inventor name: LOGIER, REGIS

Inventor name: PIERONNE, ALAIN

GRAA (expected) grant

Free format text: ORIGINAL CODE: 0009210

AK Designated contracting states

Kind code of ref document: B1

Designated state(s): AT BE CH DE FR GB IT LI NL SE

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: SE

Effective date: 19881012

Ref country code: NL

Effective date: 19881012

Ref country code: AT

Effective date: 19881012

REF Corresponds to:

Ref document number: 37790

Country of ref document: AT

Date of ref document: 19881015

Kind code of ref document: T

REF Corresponds to:

Ref document number: 3474512

Country of ref document: DE

Date of ref document: 19881117

GBT Gb: translation of ep patent filed (gb section 77(6)(a)/1977)
ITF It: translation for a ep patent filed

Owner name: DR. ING. A. RACHELI & C.

NLV1 Nl: lapsed or annulled due to failure to fulfill the requirements of art. 29p and 29m of the patents act
PLBE No opposition filed within time limit

Free format text: ORIGINAL CODE: 0009261

STAA Information on the status of an ep patent application or granted ep patent

Free format text: STATUS: NO OPPOSITION FILED WITHIN TIME LIMIT

26N No opposition filed
PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: FR

Payment date: 19900717

Year of fee payment: 7

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: CH

Payment date: 19900723

Year of fee payment: 7

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: GB

Payment date: 19900727

Year of fee payment: 7

PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: BE

Payment date: 19900731

Year of fee payment: 7

ITTA It: last paid annual fee
PGFP Annual fee paid to national office [announced via postgrant information from national office to epo]

Ref country code: DE

Payment date: 19900914

Year of fee payment: 7

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: GB

Effective date: 19910806

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: LI

Effective date: 19910831

Ref country code: CH

Effective date: 19910831

Ref country code: BE

Effective date: 19910831

BERE Be: lapsed

Owner name: UNIVERSITE DU DROIT ET DE LA SANTE LILLE II

Effective date: 19910831

GBPC Gb: european patent ceased through non-payment of renewal fee
PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: FR

Effective date: 19920430

REG Reference to a national code

Ref country code: CH

Ref legal event code: PL

PG25 Lapsed in a contracting state [announced via postgrant information from national office to epo]

Ref country code: DE

Effective date: 19920501

REG Reference to a national code

Ref country code: FR

Ref legal event code: ST